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This is an author-deposited version published in: http://oatao.univ-toulouse.fr/
Eprints ID: 13669
Identification number: DOI: DOI:10.2174/1874120701509020026
Official URL: http://dx.doi.org/10.2174/1874120701509020026
To cite this version:
Demnati, Imane and Grossin, David and Marsan, Olivier and Bertrand,
Ghislaine and Collonges, Gérard and Combes, Christèle and Parco, Maria and
Braceras, Inigo and Alexis, Joël and Balcaen, Yannick and Rey, Christian
Comparison of Physical-chemical and Mechanical Properties of Chlorapatite
and Hydroxyapatite Plasma Sprayed Coatings. (2014) The open biomedical
engineering journal, vol. 9 (suppl.1-M3). pp. 26-39. ISSN 1874-1207
Any correspondence concerning this service should be sent to the repository administrator:
[email protected]
Comparison of Physical-chemical and Mechanical Properties
Chlorapatite and Hydroxyapatite Plasma Sprayed Coatings
of
Imane Demnati1, David Grossin1, Olivier Marsan1, Ghislaine Bertrand1, Gérard Collonges2,
Christèle Combes1, Maria Parco3, Inigo Braceras3, Joel Alexis4, Yannick Balcaen4 and
Christian Rey1,*
1
Université de Toulouse, CIRIMAT, INPT-CNRS-UPS, ENSIACET, Toulouse, France
2
PS: Projection Plasma System, Montbazens, France
3
Tecnalia, Mikeletegi Pasealekua 2, Donostia-San Sebastian, Spain
4
Université de Toulouse, INPT-ENIT, Laboratoire Génie de Production, Tarbes, France
Abstract: Chlorapatite can be considered a potential biomaterial for orthopaedic applications. Its use as plasma-sprayed
coating could be of interest considering its thermal properties and particularly its ability to melt without decomposition
unlike hydroxyapatite. Chlorapatite (ClA) was synthesized by a high-temperature ion exchange reaction starting from
commercial stoichiometric hydroxyapatites (HA). The ClA powder showed similar characteristics as the original
industrial HA powder, and was obtained in the monoclinic form. The HA and ClA powders were plasma-sprayed using a
low-energy plasma spraying system with identical processing parameters. The coatings were characterized by physicalchemical methods, i.e. X-ray diffraction (XRD), Fourier transform infrared spectroscopy (FTIR) and Raman
spectroscopy, including distribution mapping of the main phases detected such as amorphous calcium phosphate (ACP),
oxyapatite (OA), and HA or ClA. The unexpected formation of oxyapatite in ClA coatings was assigned to a side reaction
with contaminating oxygenated species (O2, H2O). ClA coatings exhibited characteristics different from HA, showing a
lower content of oxyapatite and amorphous phase. Although their adhesion strength was found to be lower than that of
HA coatings, their application could be an interesting alternative, offering, in particular, a larger range of spraying
conditions without formation of massive impurities.
Keywords: Chlorapatite, FTIR, hydroxyapatite, low energy plasma spraying, mechanical testing, Raman, XRD.
INTRODUCTION
Orthopaedic implants, especially those intended to
restore the function of load-bearing joints (hip, knee,
shoulder, elbow, ankle, finger...) of aged or injured human
beings, should possess several attributes to meet the high
level of mechanical stresses, wear, and fatigue in the course
of normal activity. Although they may differ depending on
the type of joints, these attributes include mechanical
properties (elasticity, yield stress, ductility, toughness, and
wear resistance) as well as biological properties
(biocorrosion resistance, biocompatibility, good and longterm osseointegration). Metallic materials are most
commonly used for load bearing implants. Stainless steel,
cobalt alloys and titanium alloys are accordingly
commercially available for bone substitutes, artificial joints
and dental implants [1, 2]. Durability and functionality of the
implant are governed mainly by the properties of the bulk
material, whereas the biological response depends, among
*Address correspondence to the author at the Université de Toulouse,
CIRIMAT, INPT-CNRS-UPS, ENSIACET, Toulouse, France;
Tel: +33 5 34 32 34 84; Fax: +33 5 34 32 34 98;
E-mail: [email protected]
others, on the surface characteristics of the implantable
device. Indeed, a crucial step for the implant stability is the
formation of the effective interface between the bone and the
implanted material. Several surface characteristics favour
this osseointegration: mechanical interlocking related to
surface roughness and physical characteristics, and direct
chemical interactions involving bonds between the implant
surface and bone tissue constituents. To promote the
osseointegration of metallic implants, morphological (3D
texturing, surface roughness and porosity) and chemical (ion
implantation, grafting, and coating) modifications of the
implant surface have been proposed [3, 4]. Since the mid1980s, plasma sprayed hydroxyapatite (HA) (Ca 10(PO4)6
(OH)2) coatings appear as the most developed and successful
treatments of metallic, especially titanium-based, implants
for a fast integration to bone tissues [5-13]. Indeed,
atmospheric plasma spraying (APS) is the most widely used
commercial technique due to its process simplicity, low cost,
and bulk production [14]. During plasma spray, the material
to be deposited (feedstock), typically as powder, is
introduced into the core of a plasma plume emanating from a
d.c. torch. The powder is fully or partially melted, and
accelerated towards the work piece, upon which it impacts
and cools down to form a coating by overlapping of splats.
Depending on the plasma-forming gases, electrical
characteristics, feedstock attributes, and kinematics
conditions, the thermal input transferred to the in-flight
particles and coating, together with the cooling rate, can
result in severe powder decomposition and in lack of
crystallinity. Starting from HA feedstock it is noteworthy
that plasma spray can induce the formation of amorphous
calcium phosphate (ACP), tricalcium phosphate ( or TCP), tetracalcium phosphate (TTCP), calcium oxide (CaO)
and dehydroxylated products (oxyhydroxyapatite or
oxyapatite) [5, 7, 15-21]. The decomposition sequence
occurs along the powder trajectory in the plasma jet that is
determined mainly by the particles’ size, density and their
dwell-time in conjunction with many parameters, for
example the viscosity and density of the plasma. The degree
of crystallinity of plasma sprayed HA coatings is usually
between 65 and 85 vol. % (in some operating conditions it
may reach 93 vol. %) [7, 15, 22-26]. Crystalline HA is seen
as a crucial factor for long-term coating stability in vivo.
Although the presence of relatively soluble non-apatitic
calcium phosphate salts such as ACP, TCP, and TTCP has
been found to accelerate the bone attachment, these phases
are related to long-term non-uniform coating degradations
that adversely affect the prosthetic stability of the implants
[4, 27-34]. To limit the amount of easily soluble CaP phases,
the steep temperature gradients during plasma spraying have
to be reduced by increasing the substrate temperature and
controlling the cooling rate and/or by limiting the thermal
transfer. One method to control the degree of melting of the
powder could be achieved by micro plasma spray (MPS, also
called MIPS) or low-energy plasma spray (LEPS) techniques
[35-42]. Due to the low heat input of these plasma torches,
overheating of the powder particles as well as excessive local
overheating of the coating can be avoided. LEPS also allows
the production of highly porous (around 20 vol. %)-thick
coatings (about 250 µm) without accumulation of residual
stresses (tensile stresses are detrimental because they
promote cracks and accelerate dissolution) and without
negatively affecting the mechanical properties (fracture
toughness of about 0.6 MPa.m½). In a previous work, we
have implemented such an innovative low energy plasma
spray system that has resulted in producing thin dense HA
coatings with a good degree of crystallinity (around 70%)
and improved purity, compared to conventional high-energy
APS coatings, as demonstrated by Raman studies [43].
Another strategy to overcome the decomposition of HA and
thus limit the presence of soluble CaP phases is to use
calcium apatites with higher thermal stability such as
fluorapatite (FA) or chlorapatite (ClA) [44-48]. Indeed, it has
already been demonstrated that both materials lead to
coatings with superior adhesive strength to the substrate as
well as without significant thermal degradation. Fluorapatite
and fluorhydroxyapatite (FHA) as raw material or coatings
have been extensively studied [45-47]. In vitro tests have
demonstrated the ability of such material to favour the
osteoblast attachment, to support the cytocompatibility, to
exhibit an antibacterial effect, and to stimulate cell
proliferation and differentiation. In weight-bearing model (in
vivo), no statistical difference in loss of ceramic coating was
found between HA and FA coatings and durable implant
fixation was always concluded.
The objective of the current study is to compare
chlorapatite and hydroxyapatite coatings obtained by a LEPS
gun. Until today only a few authors have worked on the
substitution of chloride ion in hydroxyapatite, and no
commercial product is available. Hence, our first aim was to
develop a simple and fast reaction synthesis transposable at
an industrial scale. A method is first described to prepare
easily chlorapatite from commercial HA preserving similar
powders characteristics. The main physical-chemical and
mechanical properties of the coatings obtained with a low
energy plasma spraying process are compared using
standardized procedures and specific techniques such as
Raman microscopy mapping of the main mineral phases
found in the coating and three points mechanical bending
with stiffener.
POWDERS PREPARATION AND CHARACTERISTICS
The hydroxyapatite used in this study was a commercial
product (Teknimed, L’Union, France). The XRD analyses,
according to ISO standard (ISO 13779-3: 2008), did not
detect any crystalline impurity (Fig. 1) and the FTIR
spectrum (Fig. 2) was the same as that of stoichiometric
hydroxyapatite.
Regarding the synthesis of chlorapatite, several methods
have been proposed [49, 50]. Precipitation methods in
aqueous media do not lead generally to stoichiometric
chlorapatite and the apatite obtained contains always
hydroxide ions. Several dry synthesis methods giving
stoichiometric ClA with a high purity have been proposed.
The reaction of CaCl2 on Ca3(PO4)2 (800-1100°C) [50]
results in ClA with a high yield, especially when using an
excess of CaCl2, which can be removed by washing. Other
methods can be used, especially Cl-OH ion exchange
reactions on HA (800-1100°C), which offers the advantage
of using an existing commercial product. Several
chlorinating agents can be used for this exchange reaction,
such as CaCl2:
CaCl2 + Ca10(PO4)6(OH)2 → Ca10(PO4)6Cl2 + CaO + H2O (1)
This reaction leads to the formation of CaO, which is
difficult to remove. Other chlorinating agents could be used
and more interestingly, chlorinating gases, such as HCl,
which would not produce any residues except water. This
reaction has been studied by Hoekstra [49] at about 1050°C
and has been shown to lead to formation of stoichiometric
ClA:
Ca10(PO4)6(OH)2 + HCl ↔ Ca10(PO4)6Cl2 + H2O
(2)
This reaction is supposed not to alter the powder
characteristics (e.g. grain size, shape). One of the difficulties
in such a reaction is to handle hydrogen chloride gas, and, to
overcome this difficulty, we choose as a precursor of HCl,
NH4Cl which decomposes at about 340°C under atmospheric
pressure, into NH3 and HCl. In such a synthesis we should
keep in mind, that non-stoichiometry has been reported to
occur in ClA heated at high temperature, which has been
assigned to the release of CaCl2 [51]:
Ca10(PO4)6Cl2 → Ca10-x(PO4)6Cl2-2x + xCaCl2
(3)
Previous attempts to use the reaction of HA with NH4Cl
by A. Hoekstra [49] have probably failed to produce
stoichiometric ClA because the treatment temperature
(1180°C) was too high. The second point to consider is the
fast hydrolysis of ClA into HA when traces of water
molecules are present. Thus, we shall use a temperature as
low as possible, resulting in a reasonable reaction rate and
enabling to preserve a dry atmosphere.
The ion exchange reaction was performed in a tubular
oven under a flux of dry nitrogen enriched with sublimated
NH4Cl in large excess placed in a zone of the tubular oven at
about 400°C [52]. The unreacted HCl in the gas flow
recombines with NH3 and regenerates NH4Cl, which
crystallizes at the outlet of the oven and could possibly be
recycled. The reaction was fast at 950°C and a few grams of
HA were transformed into ClA in about 15 minutes.
However, for production treatments of the order of several
hundreds of grams on partly sintered HA grains of industrial
HA the treatment time was two hours [52].
the other hand, chlorinating treatments have been shown to
remove several impurities present in the apatite structure as
volatile chlorides and this reaction has been proposed for the
extraction of transition elements, rare earths and uranides
from apatitic ores [54]. Although we did not determine the
effect of the chlorination treatment on the level of impurities,
this possibility could be an interesting additional advantage
of the chlorination treatment.
FTIR data (Fig. 2) confirm the removal of the OH- ions,
the stretching (3570 cm-1) and librational (633 cm-1) lines of
which cannot be seen on the spectra after chlorination. The
lines characteristic of OH-Cl interactions in solid-solutions
of HA and ClA, at 3495, 3510 cm-1 [55] cannot be observed
either, suggesting a complete replacement of OH- ions by Clions in the apatite structure.
The XRD analyses (Fig. 1) of the samples obtained
indicated the formation of chlorapatite in its monoclinic
form, which is the stable low temperature isomorph. The
monoclinic ClA has been shown to correspond to an order
among the Cl- ions of the chlorapatite [53]. The tiny peaks of
the superstructure related to this ordering can be distinctly
seen on the XRD diagram Fig. (1). The transition
temperature to the hexagonal structure of ClA occurred as
expected at about 200°C. The unit cell dimensions (Table 5)
appeared consistent with that of a stoichiometric
chlorapatite.
Fig. (2). FTIR spectra of the HA and ClA powders used in this
work. Apatitic phosphate absorption bands are indicated by dotted
lines.
The morphology of the HA and ClA powders are shown
in Fig. (3). Their main characteristics (Ca/P, particle size,
specific surface area, flowability) are reported in Table 1.
Fig. (1). Diffraction patterns of the HA and ClA powders used in
this work. Superlattice lines on ClA pattern are shown by arrows.
Theoretically stoichiometric HA should also exist as a
monoclinic apatite at room temperature. However, most
industrial HA crystallize in the hexagonal systems. This
anomaly is often attributed to the existence of defects and
impurities, which stabilizes the hexagonal form of HA. On
Table 1.
The grains in both samples show irregular shapes related
to the preparation of HA granules by grinding of sintered
particles and subsequent sieving. The surface irregularities
can be seen on ClA grains, which were not apparent on HA
ones. Granulometry (Malvern Matersizer 2000) revealed a
similar grain distribution for both HA and ClA powders. The
grain sizes extended from 0.7 to 140 µm with a main
distribution peak between 50 and 80 µm and smaller ones
between 0.7-3µm and 3-20 µm [52]. On chlorination, the
median grain size d0.5 has decreased, presumably due to
fragmentation of the initial HA grain during the chlorination
process. The flowability was determined, according to the
recommendations of the European Pharmacopoeia, by
measuring the flow time of 100 g of powder through a funnel
with specified dimensions [52]. The flowability of the
Main characteristics of the powders
Powders
Ca/P
Specific surface area (m2g-1)
Granulometry d0.5 (µm)
Flowability (s)
HA
1.66 ± 0.02
1.44 ± 0.07
69.5
27.26 ± 3.44
ClA
1.67 ± 0.02
1.48 ± 0.15
56.5
4.75 ± 0.32
Fig. (3). SEM images of HA (left) and ClA (right) powders.
powders appeared significantly different and this observation
might be possibly related to a change in surface
characteristics as observed by SEM, although this remains
difficult to elucidate.
In addition, Rietveld analyses of XRD data reveal that
the chlorination treatment induced, unexpectedly, a decrease
in the average size of the ClA crystals compared to the
industrial HA crystals in the starting powder (Tables 4 and
5).
Comparison of the phase diagrams, CaO-P2O5 for HA
and CaCl2-Ca3(PO4)2 for ClA [50, 56] indicate a
decomposition of HA on heating, whereby ClA melts
without decomposition. This property is a major argument in
favour of the use of ClA for producing plasma sprayed
coatings: the formation of foreign phases is expected to be
limited, except for the amorphous phase resulting of the
quenching of a melted phase.
The comparison of the solubility of HA and ClA, which
could determine possible differences in bioresorption of the
coatings, is also interesting. However, published data on ClA
solubility are scarce and provide incoherent values. Thus
ClA has been reported to be less soluble than HA [57],
although thermodynamic data strongly suggest that it should
be more soluble than HA with a solubility product pKsp(ClA)
= 108 at 25°C (pKsp(HA) = 116.8 for Ca10(PO4)6(OH)2) [58].
However, considering the concentration of Cl- ions in body
fluids of more than 105 times higher than that of OH- in
serum at physiological pH, the effect of this difference
would be minor. It should be noticed that the incorporation
of chloride ions in biological apatites, especially enamel, has
been confirmed [59].
(Switzerland). Ti substrates were previously degreased and
then sandblasted with corundum F150 using a pressure of 2
bars to produce a surface roughness (Ra) of about 1 µm.
Coupons were separately sprayed with chlorapatite or
hydroxyapatite under the same thermal spraying conditions
(Table 2). For practical reasons, the gun operated with
standard electrodes. The entire gun was cooled with water
and a glass fibre-reinforced epoxy housing separated the
electrical poles. A more detailed description of the LEPS
system has been provided elsewhere [60]. Coatings with
various thicknesses were obtained simply by changing the
number of torch runs (1, 6, 12 and 20 runs) for both HA and
ClA powders. We can see on Table 3 that the coating
thickness depended not only on the number of runs, but also
on the nature of the apatite: whatever the number of spray
runs, the HA-coatings were always thicker than the ClAcoatings. This observation can be related to the decrease of
the median grain size associated with the chlorination
treatment, and possibly to a certain additional fragility of the
grains, although other causes could be envisioned such as the
viscosity of the melted phase for example, which is supposed
to be totally liquid in the case of ClA whereas it may contain
solid CaO in the case of HA.
Table 2.
Torch characteristics and plasma spray conditions
Torch Type
Sulzer Metco; Switzerland
Powder level (kW)
15 kW
Current (A)
400
Gas
Argon
-1
Spraying velocity (mm.s )
COATINGS DEPOSITION
Thermal Spraying
The powders (HA and ClA) were sprayed in air on
surgical grade (grade 4) Ti disks (12 mm in diameter and 3
mm in thickness), using a low energy plasma spray (LEPS)
device [43]. This system was an experimental low energy
plasma spray system designed and developed by InasmetTecnalia (Spain) from commercial Sulzer Metco torch
200
Plasma gas rate (Ar; L.mn-1)
24
Stand-off distance (mm)
40
-1
Carrier gas rate (Ar; L.mn )
Powder particle size (µm)
Powder feeding rate (g.mn-1)
Number of spray runs
4
50-80
8
1; 6; 12; 20
Table 3.
Coating thickness as a function of the number of runs and of the type of apatite.
Thickness per run (µm.run-1)
Coating thickness (µm)
Number of runs
HA-coating
ClA-coating
HA-coating
ClA-coating
1
28 ± 4
16 ± 4
28 ± 4
16 ± 4
6
85 ± 4
60 ± 4
14.2 ± 0.7
10.0 ± 0.7
12
161 ± 4
120 ± 4
13.4 ± 0.3
10.0 ± 0.3
20
274 ± 4
179 ± 4
13.7 ± 0.2
9.0 ± 0.2
PHYSICAL-CHEMICAL CHARACTERISTICS OF THE
COATINGS
Structural and Chemical Composition of the Coatings
Surface and bulk composition of HA and ClA coatings
were determined. The coating surface was analysed directly
on the as-sprayed coatings. For the bulk characterizations,
the coatings were scrapped and ground as indicated in the
ISO standard (13779-3: 2008). Investigations on coating
microstructure were also performed on sample cross-sections
prepared as follows: the coupons were cut with a diamond
disc (Struers) and then the half-coupon was embedded into
an epoxy resin under vacuum. The embedded cross-sections
were polished using a silicon carbide paper (1000 and 1200
grade SiC paper). Further polishing was conducted using
2400 then 4000 grade SiC paper to obtain a flat surface
suitable for analysis.
X-ray Diffraction Analysis of the Coatings
Standards have been published concerning the coating’s
chemical composition (Ca/P ratio), phase composition, and
crystallinity (ISO 13779-2 and 3:2008). These standards are
based essentially on X-ray diffraction (XRD) analyses.
X-ray diffraction studies on both powders and coatings
were carried out in order to identify the composition of the
coating (obtained after 12 spray runs) and determine its
crystallinity, according to the ISO 13779-3: 2008 standard. A
Seifert XRD-3000 diffractometer (Germany) with a CuK
radiation over a 2 range of 20-65° was used. Patterns were
collected at a step increment of 0.02°, with a collection time
of 24 seconds at each step. According to the standard, the
HA-coatings crystallinity (Cr) was defined as the ratio
between the sum of integrated intensities of ten diffraction
lines (Ahkl) of the coating diagram, and of the same ten
lines of a fully crystalline HA reference powder (A0hkl): Cr
= (Ahkl)/ (A0hkl). The same approach was used to
determine the ClA coating crystallinity. However, the (102)
line used in crystallinity determination of HA is weak in ClA
and it has a minor contribution in the crystallinity index; thus
it was replaced by (201) line. Both coatings diagrams can be
indexed in the hexagonal system indicating that a change of
the structure of sprayed ClA powder has occurred. As we
will see later, this structural modification is related to the
alteration of the ClA crystals in the coatings and the
formation of oxyapatite (OA) as well.
For both coatings, we noticed an increase of the full
width at half maximum (FWHM) value of the diffraction
lines compared to that of the initial powders (Figs. 4 and 5),
which is generally assigned to two main phenomena: the
decrease of the crystallite size, and the increase of the
microstrain. In order to evaluate these contributions,
Rietveld refinement analyses were performed using MAUD
software. The crystallographic parameters determined for the
HA and ClA initial powders and for the 12-run HA- and
ClA-coatings are reported in Table 4 and Table 5, respectively.
For HA- and ClA-coatings, we can notice both a significant
increase in micro-strains and a decrease in crystallite size.
However, these observations and the related calculations
neglect an important cause of line broadening associated
with the formation of heterogeneous solid solutions of oxyhydroxyapatite and oxy-chlorapatite, which would result in
broadened diffraction lines, corresponding to the sum of
unresolved diffraction peaks of individual crystalline
domains considered as homogeneous. For the OClA this
effect would result in a higher broadening of diffraction lines
than for OHA, due to larger differences in unit-cell
dimensions between OA and ClA [60]. The average unit-cell
dimensions for ClA coatings can be compared to that of the
powder considering that b=2a in the monoclinic ClA
powder. The formation of solid solutions (OHA or OClA)
can be related to a clear decrease of the a unit-cell
dimensions noticed on the coatings. This effect appears
Fig. (4). X-ray diffraction patterns of HA powder and coating (12
spray runs).
Table 4. Crystallographic parameters of HA powder and HA coating (12 spray runs). (The pattern obtained with Rietveld
refinement of a HA coating is given as supportive material).
Table 5.
Space group: P63/m
HA-powder
HA-coating
a (Å)
9.4157(2)
9.4107(2)
c (Å)
6.8865(2)
6.8748(2)
Crystallites size (µm)
0.4025(171)
0.2030(67)
Microstrain (rms)
0.00058(2)
0.00099(2)
Rexp (%)
5.47
6.00
Crystallographic parameters of ClA powder and ClA coating (12 spray runs).
Space group: P21/c
ClA-powder
ClA-coating
a (Å)
9.652(1)
9.550(3)
b (Å)
19.319(2)
-
c (Å)
6.784(1)
6.818(2)
 (°)
120.00(2)
-
Crystallites size (µm)
0.1467(39)
0.0747(20)
Microstrain (rms)
0.00106(3)
0.00135(3)
Rexp (%)
6.30
5.85
stronger for OClA due to the strong difference in unit-cell
dimensions of ClA and OA just mentioned. However, in the
case of ClA coatings, another possibility for the variations of
the unit cell dimensions, compared to those of the ClA
powder, would be the formation of a non-stoichiometric ClA
at high temperature due to the release of CaCl2 [51].
higher crystallinity ratio than HA-coating, although it was
not determined in the same way. This observation should not
be only related to the amount of amorphous phase formed in
the coatings. Other causes can produce crystallinity
variations such as fast recrystallization of small apatite
crystals from the melt or the amorphous phase, or the
formation of solid solutions with OA.
The Ca/P ratio of HA- and ClA-coatings obtained after
12 spray runs was determined according to the ISO 13779-3:
2008 standard on a scraped and ground coating, which had
been heated at 1000°C during 15 h. The XRD patterns
showed only apatite crystals for both HA- and ClA-coatings,
indicating that plasma spraying using the LEPS system did
not appear to alter the stoichiometry of the apatite.
Vibrational Spectroscopy Analysis of the Coatings.
Fig. (5). X-ray diffraction patterns of ClA powder and coating (12
spray runs).
The calculated crystallinity ratio, determined according
to the standard, was equal to 68% for HA-coating and to
98% for ClA-coating. The ClA-coating showed a much
Several additional characteristics of the apatite coatings
are more difficult to determine using X-ray diffraction
analyses: the main phase proportions and their distribution
within the coating, and, more importantly, the amount of
amorphous phase, which is not specifically considered in the
ISO standard, although it could determine the coating
behaviour in vitro and in vivo. A more accurate
characterization of HA and ClA powders and the related
plasma sprayed apatite coatings can be proposed, using
vibrational spectroscopies [61], Fourier transform infrared
spectroscopy and Raman spectroscopy, with a special focus
on Raman micro-spectroscopy imaging on HA- and ClAcoatings.
FTIR Spectroscopy Characterization
Both initial HA and ClA powders and scraped HA- and
ClA-coatings were analysed by transmission Fourier
transform infrared (FTIR) spectroscopy (Nicolet 5700
spectrometer, ThermoElectron) using KBr pellets. We
examined especially the 1100-950 cm-1 (1PO4 and 3PO4)
and 600-450 cm-1 (4PO4) domains, corresponding to the
different phosphate vibration bands. In these domains, FTIR
spectra of both HA- and ClA-coatings Figs. (6 and 7)
showed broader and less resolved bands than that of the
initial powders. This phenomenon can be related to a
decrease in crystallinity. The enhanced relative intensity of
bands observed in the 2PO4 domain (434 and 471 cm-1), in
the spectrum of the HA coating, can be correlated to the
splitting of the 1PO4 band and the decrease in the relative
intensity of the OH bands at 3572 and 630 cm-1
(Fig. 6) which have been shown to correspond to the
formation of oxyapatite [61]. Although less visible than in
HA, the formation of oxyapatite is also apparent on FTIR
spectra of ClA coatings (Fig. 7) which exhibit lines with a
higher intensity in the 2PO4 domain than the starting
powder.
especially the most important ones, in some instances with
better sensitivity than according to XRD analyses [52]. In
addition, Raman scattering imaging allows local
investigation of the coating’s heterogeneity [52, 62]. The
1PO4 domain, with strong thin lines, seems well adapted for
imaging [6, 63]. The amorphous calcium phosphate (ACP)
especially is characterized by a broad Raman line around 950
cm-1 and all crystalline phases show lines distinct from that
of apatite at 961 cm-1. The xyapatite (OA), rather difficult to
distinguish by other methods, exhibits very specific Raman
scattering lines at about 951 cm-1 and 966 cm-1 [64]. The
only phase that cannot be detected in this domain is CaO.
Fig. (7). FTIR spectra of ClA powder and coating.
Fig. (6). FTIR spectra of HA powder and coating.
Raman Spectroscopy Characterization
All phases detected in a plasma-sprayed coating of HA
can theoretically be distinguished by Raman spectroscopy,
Fig. (8). Raman spectra of HA powder and coating.
Both initial HA and ClA powders and the as-prepared
HA- and ClA-coatings were analysed by Raman
spectroscopy in the range of 100-1200 cm-1 and 3500-3600
cm-1 (Horiba Jobin-Yvon HR 800 spectrometer equipped
with a helium-neon laser: = 632.8 nm). The quantitative
evaluation of the components of the 1PO4 band was
performed using LabSpec 5 software (Horiba). The 1PO4
band Raman spectra were decomposed according to the same
protocol for all the samples in order to facilitate their
comparison [52]: a baseline correction was performed on
each spectrum. Peak positions and some curve-fitting
parameters were recorded and used as initial input in the
curve-fitting program. Iterations continued until the best fit
was obtained.
Fig. (9). Raman spectra of ClA powder and coating.
The Raman spectra of HA and ClA scrapped coatings are
presented in Figs. (8) and (9) together with those of the
initial powders. The most intense Raman line, 1PO4,
appeared the most altered after spraying. The integrated
intensity of the different contributing sub-bands has been
determined to estimate quantitatively the changes induced by
spraying. The resulting curve-fittings are presented in Figs.
(10) and (11) for HA- and ClA-coatings respectively. The
detection of oxyapatite phase in both coatings confirmed the
results obtained by FTIR spectroscopy; however, the
proportion of OA appears always significantly less important
in ClA than in HA coatings. The same observation is true for
the amorphous phase.
Fig. (10). A-Gaussian-Lorentzian curve fitting of the ν1PO4 Raman
stretching domain of HA coatings (20 spray runs), with the LEPS
plasma gun. (1) ACP: amorphous calcium phosphate; (2) and (4)
OA: oxyapatite; (3) HA: hydroxyapatite.
An accurate mapping of the different phases in apatite
coatings can be obtained by micro-Raman imaging involving
curve fitting in the 1 PO4 domain, extraction of the
characteristic line(s) associated with specific phases, and of
their relative intensities [52]. It should be noticed that at this
stage, without accurate standardization, and due to
uncertainties in decomposition results. The data do not
represent the real content of phases present in the coating but
offer a base for visualizing the phase distribution in a first
semi-quantitative approach. Figs. (12) and (13) show the
main constituents distributions, i.e. HA or ClA, OA and
ACP, in the cross section of HA and ClA coatings. The
heterogeneity in the distribution of the constituents is
immediately apparent. Domains with a high content in HA
appear to be embedded in an amorphous phase acting as a
binder. These observations are consistent with other
descriptions of phenomenon occurring during plasma
spraying [4, 5, 63, 65]. The nodules of HA, which appear as
well delimited zones, are believed to correspond to the
unmelt cores of the splats. In some cases smaller HA
domains grouped in a zone may appear, corresponding
possibly to the crash and dispersion into smaller particles of
the solid core of splats impacting the substrate or to
recrystallization of HA from the melted or amorphous phase.
The OA rich domains are distributed more uniformly than
the HA nodules and do not form well-defined zones with
dominant concentrations. This distribution could result of a
recrystallization process in the melted part of the splats,
possibly associated with a direct formation of OA in the
unmelt cores.
For ClA coatings the layered structure of the coating
related to the splat accumulation is more apparent than in
HA coatings, especially in the ACP mapping. The ClA
domains appear elongated and rather diffuse, indicating a
better spreading of the splats; they are surrounded by the
amorphous phase. The OA seems more homogeneously
distributed at the surface of ClA domains or within
amorphous domains; in these domains, zones very poor in
ClA and rich in OA can be clearly observed, suggesting that
AO forms mainly in a recrystallization processes of the
molten phase or the amorphous phase.
Fig. (11). A-Gaussian-Lorentzian curve fitting of the ν1PO4 Raman
stretching domain of ClA coatings (20 spray runs), with the LEPS
plasma gun. (1) ACP: amorphous calcium phosphate; (2) and (4)
OA: oxyapatite; (3) ClA: Chlorapatite.
Therefore, Raman micro-spectroscopy can be used as a
routine non-destructive tool to obtain rapid analysis of the
composition of apatite coatings and even of different
domains of a splat. This technique could be adapted for the
chemical characterization of the coating directly on
biomedical implants. Image analyses could then be used to
describe the coating characteristics with accuracy.
10
8
Surface Roughness
MECHANICAL PROPERTIES
The coating surfaces and cross-sections were studied by
scanning electron microscopy (SEM). The coating crosssections were carbon coated, then SEM micrographs were
recorded in the secondary electron mode using a LEO 435
VP microscope. The typical surface morphologies of the assprayed HA- and ClA-coatings (12 spray runs) are presented
as supportive materials.
Several methods can be used to determine the adherence
of a coating to its substrate. Concerning calcium phosphate
coatings, an adherence measurement test was standardized
(ASTM C633-01, ISO 13779-4) and the results obtained
according to this procedure will be first presented. Among
other methods used, the three point bending with a stiffener
has also been applied and will be discussed.
Ra (mm)
The average roughness of the ClA and HA coatings was
determined by optical interferometry (Zygo) as the average
of four measurements. The surface arithmetic roughness of
HA and ClA coatings (Ra) was determined as a function of
the number of spray runs Fig. (14). Ra increases strongly
after the first run and reaches rapidly a constant value
depending on the nature of the apatite: it is always higher in
HA coatings than in ClA coatings. The increase of Ra is
commonly observed and has been related to the structure of
splats generally smaller at the fringe and larger in the centre
[66]. These data indicate that HA splats are globally thicker
than ClA ones, and seem consistent with the variations of the
coating thickness according to the number of runs. The
difference between HA and ClA coatings could be due, in
part, to the alteration, already mentioned, of the particle size
related to the chlorinating treatment.
6
4
2
0
0
1
6
12
20
Number of spray traverses
Fig. (14). Surface roughness of the coatings vs. number of sprayruns (0: initial roughness of Ti plate).
Fig. (12). Raman spectroscopy mappings of HA, OA and ACP in hydroxyapatite coatings. Light blue oval: domain rich in HA, poor in ACP
and with a little OA, tentatively associated with an unmelt core of a splat. White circle: domain rich in OA, poor in HA, with some ACP,
attributed to the recrystallization of a molten domain or recrystallization of solid ACP phase.
Fig. (13). Raman spectroscopy mappings of ClA, OA and ACP in chlorapatite coatings. Light blue oval: domain rich in ClA, poor in ACP
and OA, tentatively associated with an unmelt core of a splat. White circle: domain rich in OA, poor in HA, within two ACP layers,
attributed to the recrystallization of a molten domain or of solid ACP phase. The layered structure of the splats is clearly visible on ACP
maps (the top surface is corrupted by the spectra of the embedding resin).
the mechanical properties of all the materials implied in the
elaboration of the samples: substrate, coating, and bulk
stiffener Young’s modulus, as well as the thickness and
elastic properties of a possible interphase between the
coating and the stiffener. Once these parameters are
determined, critical shear stress and critical strain energy
release rate of the substrate coating interface can be
determined from experimentally measured critical load,
thanks to analytical and/or numerical models [68]. This
complexity led us, as many authors [69, 70] to consider this
practical adhesion test as a comparative test, considering
critical load Fmax an indicator of adhesion.
Tensile Strength (ASTM C633-01, ISO 13779-4)
Test samples were made on 25 mm disks coated with HA
or ClA (12 spray runs). These coated disks were glued to a
dummy cylinder with the same diameter with FM1000 glue,
(Cytec, NJ, USA) applied at 200°C for 90 to 100 minutes.
The ultimate tensile strength of the assembly was determined
on an Instron instrument, without pre-loading at a traction
rate of 1mm/minute. The data obtained (mean of six
measurements) are presented in Table 6. There was no
significant difference between ClA and HA coatings. The
failure appeared mainly cohesive for HA coupons (it
occurred at the interface between the coating and the
substrate), and it was mixed cohesive (at 80%) and adhesive
for ClA coupons.
Table 6.
The tests were performed on corundum-blasted titanium
coupons plasma-sprayed at 12 spray runs. The stiffener was
casted in a silicon mould, directly on coated samples. The
mechanical test apparatus used in this experiment consists in
an electromechanical Instron test machine fitted with a load
cell capacity of 500 N. The crosshead speed is set to 0.5 mm.
min-1. A schematic illustration of the testing conditions is
given as supportive material. Ten samples were successfully
tested for ClA coatings, only eight for HA and two of them
had the rupture of the stiffener itself. Load versus displacement
curves are displayed on Fig. (15). To check the quality of the
stiffener, we measured the stiffness of the sample. It was
found to be 319 ± 16.9 N.mm-1 for HA coatings and 305 ±
9.83 N.mm-1 for CIA coatings. These preliminary results
confirmed the good quality of the polymeric stiffener.
Tensile strength of the coatings obtained at 12 spray
runs
Coating
Tensile bond strength (MPa)
HA
8.9 ± 1.5
ClA
8.2 ± 2.2
The ultimate loads observed are in the lower range of
those reported for HA coatings obtained by plasma spraying
[65]. The main drawback of this basic standardized test is the
diffusion of the glue in the porous coating and its limitation
to rather thick coatings (above 0.38 mm). Other measurements
were performed especially the three point bending with
stiffener.
An abrupt decrease in load-displacement behaviour was
observed beyond Fmax. The maximum load Fmax achieved
before rupture of the substrate-coating interface, thanks to
the geometrical effect generated by the stiffener, is the
indicator of the practical adhesion. For HA, Fmax = 165 ±
30.7 N (18.6 %), and for ClA, Fmax = 128 ± 7.92 N (6.16 %).
Coatings exhibited mixed modes of failure (cohesive and
adhesive). By image analysis on Energy-dispersive X-ray
spectroscopy (EDX) maps, adhesive failure was estimated to
be closed to 65% for both HA and ClA deposits. (EDX maps
are given as supportive material)
Three Point Bending Test with Stiffener
This test was developed particularly by A. Roche et al.
[67] and lead to the ISO 14679-1997 standard. It is designed
to determine adhesive or cohesive properties of paints,
varnish and others coatings. A stiffener epoxy resin
(Araldite® AW134B with HV997 hardener) is cured onto the
coated substrate in accordance with the standard to generate
a stress concentration at the interface substrate-deposit. Such
loading is known to produce mainly shear stress at the
substrate/coating interface and appears more consistent with
the surgical use of coated prosthesis. The determination of
the critical shear stress of the interface requires, without
considerations to the actual geometry of the sample, to know
200
CIA 1
CIA 2
CIA 3
CIA 4
CIA 5
CIA 6
CIA 7
CIA 8
CIA 9
CIA 10
150
Load (N)
Load (N)
100
The data reveal some differences between HA and ClA
coatings obtained in similar deposition conditions with
powders showing slightly different characteristics:
200
HAP 1
HAP 2
HAP 3
HAP 4
HAP 5
HAP 6
HAP 8
HAP 9
150
DISCUSSION
50
100
50
0
0
0
0.2
0.4
0.6
0.8
Crosshead displacement (mm)
1
0
0.2
0.4
0.6
0.8
Crosshead displacement (mm)
Fig. (15). three point bending tests loading curves for HA (left) and ClA (right) coatings.
1
-
Formation of oxyapatite occurs in both coatings but ClA
coatings exhibit much lower OA contents than HA.
-
ACP content is also lower in ClA coatings compared to
HA ones.
-
Thickness of the coatings for the same number of spray
runs is higher for HAp than for ClAp;
-
Surface roughness is higher in HA than in ClA
Mechanical properties appear also slightly different,
showing lower strength in ClA than in HA coatings in a
three point bending test with stiffener, although
adherence tests according to the ISO standard 13779-4
did not revealed significant differences.
HA and ClA Powder Characteristics
The different physical characteristics of the HA and ClA
coatings, for identical spray conditions, could be related to
slight changes in the powder characteristics and specific
differences in the apatites involved. The chlorination
treatment was expected to preserve the crystal size and grain
characteristics. Actually, the reverse treatment (the
hydroxylation of ClA) on monocrystals allowed the
preparation of HA monocrystals and its crystal structure
determination [71], this ability of high temperature ion
exchange reactions to preserve the crystalline structure
having been recently confirmed [72]. This is not observed in
our chlorination experiments and a significant decrease of
the crystal size of the initial HA was observed during its
transformation into ClA. The role of the change in unit-cell
volume between HA and ClA could be involved, although it
represents only 3.6 % of the total volume. It shall be noticed,
however, that the change in unit cell dimensions between
HA and ClA involves a decrease of the c dimension and an
increase of the a dimension. These opposite variations in
partly sintered grains could lead to a rupture of the initial
crystals and eventually of the grains. The reduction of
roughness in ClA coatings compared to HA ones, even for
one spray run, indicates a better spreading of the splats,
possibly due to a lesser amount of matter and/or higher
content of liquid phase and/or a lower viscosity. The slightly
lower melting point of ClA (1530°C) compared to that of
HA (1570°C), according to phase diagrams, together with a
smaller grain and crystal size, could facilitate its melting
within sprayed grains, although other considerations on heat
transfers in the plasma flame have also to be taken into
account [73].
Oxyapatite Content
The strong differences between Raman spectra of HA
and OA have been assigned to variations of the local
environments of phosphate ions, i.e. OH- ions in HA and
lattice vacancies or O2- ions in OA. Involving a, correlative
alterations of the vibrational energy level of the phosphate
ion in the apatite lattice. The formation of OA in HA
coatings is generally attributed to the dehydration of HA
during heating. Actually, OA is not considered to exist as a
separate phase but as a solid solution, OHA
(oxyhydroxyapatite). Raman spectra do not allow to
discriminate easily between solid solution of OHA and
mixtures of HA and OA phases. However, Raman mapping
reveals micro-domains containing both HA and OA
environments, thus supporting the existence of solid
solutions. In addition, very strong spatial variations are
evidenced indicating a strong heterogeneity. The formation
of OA environments appears as an intermediate stage before
the decomposition of HA into TTCP and TCP takes place. A
second process of formation of OA environments is due to
the recrystallization of apatite in a melt practically deprived
of OH- ions. The existence of domains very rich in OA and
very poor in HA are consistent with this recrystallization
process.
The formation of OA in ClA coatings is rather puzzling
as there is no precursor of oxygenated species. Thus in ClA
coatings the formation of OA involves necessarily a reaction
with a contaminant. A reaction may be proposed with
residual water molecules remaining in the ClA powder,
which was stored and manipulated in air. In fact, this is the
reverse reaction of the chlorination synthesis, which has
been used to synthesize hydroxyapatite monocrystals:
2H2O + Ca10(PO4)6Cl2 ↔ Ca10(PO4)6(OH)2 + HCl ↔
Ca10(PO4)6O +H2O + HCl
(4)
Such a reaction involves the formation of HA as an
intermediate phase. Although there is no detection of OH ions in the ClA coatings by Raman or FTIR spectroscopy,
this reaction could occur in the plasma or on the surface of
the coupon during cooling in air.
A second possible reaction would be the direct oxidation
of ClA with O2 from air:
O2 + Ca10(PO4)6Cl2 ↔ Ca10(PO4)6O + Cl2
(5)
although this analogue of Deacon’s reaction [74] has never
been reported in ClA. This reaction would occur preferably
at the surface of splats during the cooling stage, when in
contact with the air.
Other reactions might be possible between TiO2 at the
surface of the substrate and ClA. However, OA is distributed
in the coating thickness and does not localize especially in
close proximity to the titanium surface. OA rich domains are
always observed in domains isolated from ClA rich ones,
with no clear gradation, suggesting a preferential formation
of OA in a recrystallization process from the molten phase,
which would facilitate oxygen diffusion and reaction. The
mode of formation of OA in ClA coatings, which implies
reactions with contaminants, explains why these contain
significantly less OA than the HA ones, where OA formation
is a part of the thermal degradation.
Amorphous Phase Content
Concerning the formation of ACP, the Raman
spectroscopic data appear more reliable than the crystallinity
measurements done by XRD following standards. As already
mentioned before, several causes may be behind the decrease
in XRD crystallinity observed in the coatings, of which ACP
formation is only one. On the contrary, the significant shift
in the Raman 1 PO4 of ACP, compared to that of apatite HA
or ClA (-12 cm-1), appears as a distinctive characteristic of
the amorphous phase. However the broadness of the
amorphous PO4 lines in Raman spectra and the
superimposition with an OA line, do not allow a very
accurate quantitative evaluation. The formation of ACP is
assigned to the rapid cooling of the molten grain reaching the
surface. However, a recrystallization process is supposed to
either happen during the cooling of the splat or during an
additional upper layer spray run, involving a local re-heating
of an underlying amorphous phase. Thus, a difference in
ACP content could be related to different ratios of molten
phases and/or different rates of recrystallization. All these
phenomena are related to heat transfer in the plasma or in the
coating, which are difficult to evaluate and control, although
simulations have been proposed [73]. Several spray
parameters such as the angle of spraying; the spray distance
and the plasma gas flow rate have been shown to determine
the amorphous content of coatings [25]. However, these
parameters were maintained constant in this study. A crucial
parameter seems to be the particle size, which is related to
strong amorphous phase variations [25]. The characteristics
of ClA powders compared to HA ones (lower melting point,
smaller grain size and crystal size) should favour the
formation of coatings with a higher content in amorphous
phase, which is not observed. Therefore, the recrystallization
rate could be a determining factor in the ACP content in
these experiments.
Different recrystallization processes may occur in
coatings: crystal formation directly from the melt or in solid
state, from the ACP phase. The recrystallization in the melt
is expected to be a faster process, although it can be
interrupted by the rapid cooling and solidification of the
splat. Recrystallization from the melt could be easier in the
case of ClA as it does not involve intermediate phases like
those theoretically observed in HA recrystallization
according to phase diagrams. The recrystallization from the
amorphous solidified phase would then follow and may
occur at a rather low temperature. In HA coatings for
example, the recrystallization of ACP has been observed at
about 700°C [75]. The low recrystallization temperature
could also occur when a new hot layer is deposited on a cold
one, due to the low thermal conductivity of apatites.
Mechanical Properties
The difference in mechanical properties between ClA and
HA coatings is especially apparent in the three point bending
test with stiffener, which seems more reliable than the
standardized test. The adhesive strength of coatings has been
correlated to the porosity of the coatings, the presence of
cracks related to stresses due to differences in thermal
coefficient expansion, and its composition. In wet media,
rehydration of the coating, inducing cracks, has been
identified as a crucial parameter in the degradation of
mechanical properties. Chemical interactions between the
coating and the oxide layer of the substrate have been
suggested, but their role in the adhesion has not been clearly
identified. Concerning the phase content, it appears that a
high amount of ACP, as well as a high amount of crystalline
phase, is not favourable [76]. The weaker strength of ClA
coatings could thus be related to too high a crystallinity.
CONCLUSION
The main characteristics of ClA compared to HA
coatings is a higher content in apatite and a lower content in
amorphous calcium phosphate and oxyapatite. It is probable
that slight modifications in the coating process would permit
to limit even further the formation of OA in ClA coatings,
especially a careful elimination of water from the ClA
powder, although the role of OA in coatings is not known
and this phase should not behave differently from other
apatites. The expected advantage of ClA coatings would be a
lesser degradation in vivo. A persisting problem remains the
poor adhesion of the ClA coating on titanium substrates. In
vivo experiments have been realized and the explants are
currently examined. The first results show a direct
attachment of bone to the coating surface, as it is usually
found for this kind of coating. These results will be
published in a forthcoming report.
SUPPLEMENTARY MATERIALS
Supplementary material is available on the publisher’s
web site along with the published article.
CONFLICT OF INTEREST
The authors confirm that this article content has no
conflict of interest.
ACKNOWLEDGMENTS
This study was carried out under a MNT ERA-Net
Project named NANOMED. The authors gratefully thank the
Midi-Pyrénées region (MNT ERA Net Midi-Pyrénées
Région, NANOMED2 project) and the Institute National
Polytechnique de Toulouse (BQR INPT 2011, BIOREVE
project) for supporting this research work, especially the
financial support for research carried out in the CIRIMAT
and the LGP laboratories (France), and the Basque
government and Tratamientos Superficiales Iontech, S.A. for
their financial and technical support under the IG2007/0000381 grant for the development of the LEPS device
and deposition of the coatings carried out in InasmetTecnalia. The French industrial collaborators (TEKNIMED
SA and 2PS SA) were financed by the OSEO programs.
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